US7289601B2 - Digital image collector for X-ray systems - Google Patents

Digital image collector for X-ray systems Download PDF

Info

Publication number
US7289601B2
US7289601B2 US11/000,533 US53304A US7289601B2 US 7289601 B2 US7289601 B2 US 7289601B2 US 53304 A US53304 A US 53304A US 7289601 B2 US7289601 B2 US 7289601B2
Authority
US
United States
Prior art keywords
digital image
light
planar reflector
digital
image capturer
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Fee Related, expires
Application number
US11/000,533
Other languages
English (en)
Other versions
US20050151085A1 (en
Inventor
Jean Caseault
Min Wang
Simon Thibault
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Biokinemetrics Inc
IMASCCOPE Inc
Original Assignee
Imascope Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Imascope Inc filed Critical Imascope Inc
Assigned to IMASCCOPE INC. reassignment IMASCCOPE INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: CASEAULT, JEAN, THIBAULT, SIMON, WANG, MIN
Priority to US11/000,533 priority Critical patent/US7289601B2/en
Publication of US20050151085A1 publication Critical patent/US20050151085A1/en
Priority to BRPI0520611-1A priority patent/BRPI0520611A2/pt
Priority to CNB2005800468063A priority patent/CN100553302C/zh
Priority to AU2005312295A priority patent/AU2005312295B2/en
Priority to PCT/CA2005/001804 priority patent/WO2006058420A1/en
Priority to JP2007543668A priority patent/JP4937923B2/ja
Priority to EP05814165A priority patent/EP1829363A4/en
Priority to NZ556259A priority patent/NZ556259A/en
Priority to MX2007006530A priority patent/MX2007006530A/es
Priority to CA2589341A priority patent/CA2589341C/en
Priority to US11/763,103 priority patent/US20070237297A1/en
Publication of US7289601B2 publication Critical patent/US7289601B2/en
Application granted granted Critical
Assigned to IMASIGHT, INC. reassignment IMASIGHT, INC. CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). Assignors: IMASCOPE INC.
Assigned to BIOKINEMETRICS, INC. reassignment BIOKINEMETRICS, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: DELOITTE RESTRUCTURING INC. (TRUSTEE OF IMASIGHT INC.)
Expired - Fee Related legal-status Critical Current
Adjusted expiration legal-status Critical

Links

Images

Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
    • G01T1/164—Scintigraphy
    • G01T1/1641—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras
    • G01T1/1642—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras using a scintillation crystal and position sensing photodetector arrays, e.g. ANGER cameras
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4208—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
    • A61B6/4233—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector using matrix detectors
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N23/00—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00
    • G01N23/02—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material
    • G01N23/04—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N23/00—Cameras or camera modules comprising electronic image sensors; Control thereof
    • H04N23/30—Cameras or camera modules comprising electronic image sensors; Control thereof for generating image signals from X-rays
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N5/00—Details of television systems
    • H04N5/30—Transforming light or analogous information into electric information
    • H04N5/32—Transforming X-rays
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N5/00—Details of television systems
    • H04N5/30—Transforming light or analogous information into electric information
    • H04N5/32—Transforming X-rays
    • H04N5/321—Transforming X-rays with video transmission of fluoroscopic images
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4291—Arrangements for detecting radiation specially adapted for radiation diagnosis the detector being combined with a grid or grating
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/44—Constructional features of apparatus for radiation diagnosis
    • A61B6/4488—Means for cooling
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
    • A61B6/508—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for non-human patients

Definitions

  • X-ray systems are commonly used in medical applications to provide intrusive-free visual assessment of tissues and bones. Such systems are commonly found in hospitals, clinics and even veterinarian clinics to assist doctors in diagnosing problems with their patients.
  • X-ray systems use films exposed to an intensifying screen (also known as a phosphorous screen or fluorescent screen).
  • This screen converts the high-energy photons (X-rays) that reach the screen into lower energy photons (typically visible light), which then imprints the object being exposed onto a film.
  • the film is then developed and subsequently viewable with a suitable backlighting source, such as a light table for example.
  • a suitable backlighting source such as a light table for example.
  • the x-ray emitter 18 is fitted with an x-ray tube 22 and a collimator to help confine emitted x-rays to the area of interest.
  • the x-ray emitter 18 and film cartridge/cassette 16 are configured such that x-rays from x-ray emitter 18 will always reach the film cartridge/cassette 16 .
  • film cartridge/cassette 16 , x-ray emitter 18 and support arms 20 are slidable along the working surface 14 as a unit in the directions indicated by the arrows in FIG. 1 . This allows the operator to position the emitter/cartridge assembly as desired.
  • a generator 24 typically mounted to a nearby wall or under the table 12 supplies power to x-ray emitter 18 .
  • An alternate configuration has the intensifying screen mounted vertically, with the emitter/cartridge assembly slidable in the vertical axis, which is more suitable for chiropractors, for example.
  • working surface 14 can be made of any suitable material that facilitates the transmission of X-rays to the intensifying screen of the cartridge/cassette 16 .
  • FIG. 2 shows further details of the cartridge/cassette 16 shown in FIG. 1 , and in particular, the layered composition of the cartridge/cassette 16 .
  • cartridge/cassette 16 is positioned underneath working surface 14 of the table 12 .
  • the area of cartridge/cassette 16 is approximately 14 ⁇ 17 inches, with a thickness that is determined by the thickness of the individual layer components.
  • the cartridge/cassette 16 generally includes an optional X-ray grid 25 , an auto ionization chamber 26 , an intensifying screen 28 , and film 30 .
  • X-rays 32 pass through an object (not shown) placed on top of the working surface 14 , through the X-ray grid 25 and ionization chamber 26 .
  • Ionization chamber 26 is a device that intercepts a portion of the X-rays and sends a signal to the operator when a predetermined dose has been reached.
  • the ionization chamber 26 includes collection zones of a predetermined area that would be positioned beneath vital organs of a patient, such as lungs, to ensure that sufficient X-rays are received to obtain a satisfactory image.
  • the ionization chamber 26 effectively blocks some of the X-rays 32 from reaching the intensifying screen 28 , thus requiring an increase in the emitted dose to compensate for the absorption by the ionization chamber 26 .
  • the loss of X-rays reduces the efficiency of the system.
  • the operator places the specimen upon the table and positions the emitter/cartridge assembly. Activation of the x-ray emitter 18 at a particular energy level (kV), current (mA), and time in seconds (s), determines the delivered dose. Once the desired dose has been delivered, the film cartridge/cassette 16 is detached from the assembly and developed in a dark room.
  • kV energy level
  • mA current
  • s time in seconds
  • film-based x-ray systems include film cost, chemical developer cost, exclusive use of a room as a dark room (or the purchase of an automatic film processor), and single master copy of the image.
  • film cost e.g., film cost, chemical developer cost, exclusive use of a room as a dark room (or the purchase of an automatic film processor), and single master copy of the image.
  • this leads to further disadvantages such as storage for the film and chemicals, proper disposal for used film and chemicals, and careful packaging and mailing of the single image copy to other experts when further assessment is required.
  • a critical factor to image quality in digital x-ray systems is the ability of the CCD sensor to collect sufficient light emitted by the intensifying screen. X-ray films are positioned directly underneath the intensifying screen, and thus maximize emitted light collection.
  • a digital sensor on the other hand, must use an optical element that redirects the light from the intensifying screen onto the CCD.
  • the CCD In order to collect the complete image from the 14 ⁇ 17 inch intensifying screen, the CCD must be a certain distance apart from the screen. The distance is significant due to the large viewing angle of the optical design which redirects a 14 ⁇ 17 surface to the tiny surface of the CCD. Consequently, in most optical designs, only a small portion of the light is collected. For example, only about 2% of the light emitted from the intensifying screen will reach the CCD.
  • the electronic circuits of the CCD and those coupled to the CCD can be damaged by X-rays that pass through the working surface.
  • the CCD circuit assembly must therefore be positioned outside of the path of emitted X-rays and, depending on the positioning of the CCD circuit, redirection of the emitted photons is required.
  • the housing of the CCD sensor and its associated optics should be minimized so as not to overly limit the range of positioning of the X-ray emitter and CCD sensor assembly.
  • the X-ray assembly must be positionable anywhere along the working surface. In a chiropractor clinic, patients typically stand, therefore the X-ray assembly must be positionable anywhere vertically.
  • the most common technique includes combinations of spherical lenses that collect light over a large surface and concentrate the light beams onto one CCD chip. Unfortunately, to collect as much light as possible, it is imperative to position the lens assembly as close to the screen as possible, or use very large lenses. The resulting image distortions are significant and limit the usefulness of this technique. Furthermore, the lens design prevents the light from being evenly distributed, and more light is collected at the center of the screen than at the edges.
  • the present invention provides a digital image capturer for receiving X-rays and providing digital image data corresponding to the received X-rays.
  • the digital image capturer includes a light generator for receiving the X-rays and for emitting light in response to the received X-rays, a first planar reflector for reflecting the emitted light, a second planar reflector positioned for receiving the emitted light from the first planar reflector, and reflecting the emitted light, and a fast relay-optics system for receiving the emitted light from the second planar reflector and for focusing the emitted light onto a digital imaging device, the digital imaging device generating the digital image data.
  • the light generator can include a light shield positioned for receiving the X-rays and for blocking external light, and an intensifying screen adjacent to the light shield for emitting light in response to the X-rays passing through the light shield.
  • the light generator can include an X-ray grid mounted to the light shield, and the light shield can be constructed from a material opaque to light and transparent to X-rays.
  • the material of the light shield can be selected from the group consisting of bakelite and carbon fiber.
  • the fast relay-optics system can include a CCD electronics board having the digital imaging device, and a lens assembly positioned for receiving the emitted light from the second planar reflector, the lens focusing the emitted light onto the digital imaging device.
  • the digital imaging device can be either a CCD chip or a CMOS sensor
  • the CCD electronics board can include a microprocessor, such as a digital signal processor, for receiving digital image data from the digital imaging device and for executing image processing algorithms upon the digital image data.
  • the CCD electronics board can include non-volatile memory for storing imaging device calibration data, which can include at least one of pixel gain coefficients, pixel dark noise data, dead pixel mapping data and distortion data.
  • the lens assembly can be quasi-monochromatic and include a combination of spherical and aspherical lenses.
  • the lens assembly includes one lens coated with a 2-cavity bandpass filter made of SiO 2 and ZrO 2 to restrict light having wavelengths less than about 530 nm and greater than about 570 nm.
  • the digital image capturer further includes at least one light sensor coupled to the digital imaging device, where the at least one light sensor includes a matched lens for receiving emitted light from a specific area of the intensifying screen.
  • the first planar reflector and the second planar reflector can be housed in an imaging chamber, such that the first planar reflector is positioned at a bottom of the imaging chamber, and the second planar reflector is positioned proximate to a top corner of the imaging chamber. Furthermore, the first planar reflector is angled less than 45 degrees relative to a bottom surface of the imaging chamber. Adjustment means is coupled to the first planar reflector, the second planar reflector and the lens assembly for optimizing alignment between the first planar reflector, the second planar reflector and the lens assembly.
  • the present invention provides an auto exposure measurement system for an X-ray digital image capturer.
  • the X-ray digital image capturer emits light from an intensifying screen in response to received X-rays.
  • the auto exposure measurement system includes a light sensor, a microprocessor and a digital imaging device.
  • the light sensor receives the emitted light, and provides a signal corresponding to a level of received light.
  • the microprocessor stores a predetermined image exposure parameter for receiving the signal and compares the level of received light to the predetermined image exposure parameter.
  • the digital imaging device receives the emitted light, and is controllable by the microprocessor to generate digital image data when the level of the received light reaches the predetermined image exposure parameter.
  • the auto exposure measurement system further includes additional light sensors coupled to the microprocessor.
  • Each light sensor can include a matched lens for receiving emitted light from specific areas of the intensifying screen, and the microprocessor can store a plurality of predetermined image exposure parameters, each corresponding to a desired image type.
  • the present invention provides an X-ray system for obtaining images of materials.
  • the X-ray system includes a working surface, an X-ray emitter, a digital image capturer, a computer and a monitor.
  • the working surface has one side for mounting the materials.
  • the X-ray emitter is slidably mounted to the working surface for emitting X-rays towards an area of the working surface supporting the materials.
  • the digital image capturer is connected to the X-ray emitter and positioned on an opposite side of the working surface.
  • the digital image capturer provides digital image data corresponding to the X-rays passing through the materials.
  • the computer receives and stores the digital image data.
  • the computer provides a viewable image corresponding to the digital image data.
  • the monitor displays the viewable image provided by the computer.
  • the digital image capturer can include a light generator for receiving the X-rays and for emitting light in response to the received X-rays, a first planar reflector for reflecting the emitted light, a second planar reflector positioned for receiving the emitted light from the first planar reflector, and reflecting the emitted light, and a fast relay-optics system for receiving the emitted light from the second planar reflector and for focusing the emitted light onto a digital imaging device.
  • the digital imaging device generates the digital image data.
  • FIG. 1 shows a conventional table X-ray system of the prior art
  • FIG. 2 is an illustration of a film cartridge used in the conventional system shown in FIG. 1 ;
  • FIG. 3 is a block diagram of a digital X-ray imaging system according to an embodiment of the present invention.
  • FIG. 4 is an illustration of a digital image capturer used in the X-ray imaging system of FIG. 3 , according to an embodiment of the present invention
  • FIG. 5 is a top view of the digital image capturer of FIG. 4 ;
  • FIG. 6 is a spectral plot of light wavelengths versus energy
  • FIG. 7 is a flowchart showing an embodiment of a mehtod of the present invention.
  • the present invention provides a digital X-ray system for capturing high quality images by maximizing the collection of emitted light from an intensifying screen in response to X-ray impact.
  • the digital X-ray system includes a housing having an intensifying screen for receiving emitted X-rays and a combination of two planar reflectors for optimizing the light path between the intensifying screen and the lens assembly.
  • a CCD chip receives the light from the lens assembly, to provide a digital image for immediate on-board processing or post-processing by a computer.
  • the housing is compact, and can be used as a direct replacement for traditional film cartridges without major modifications to the system.
  • the lens assembly includes freeform matched lenses to remove any optical distortions, and the housing includes a light sensor for providing exposure measurement and feedback.
  • the system is designed to be quasi-monochromatic to maintain consistent image quality over the entire area of the intensifying screen.
  • FIG. 3 A digital X-ray system according to an embodiment of the invention is shown in FIG. 3 .
  • This particular embodiment of the present invention is illustrated in the X-ray table application previously shown in FIG. 1 .
  • Table X-ray system 100 is similar to the system shown in FIG. 1 , thus the same reference numerals refer to the same components that have been previously described for the system in FIG. 1 .
  • the film cartridge/cassette 16 of FIG. 1 is now replaced with the digital X-ray system according to an embodiment of the present invention.
  • the digital X-ray system includes a digital image capturer 102 mounted underneath working surface 14 , a power supply 104 for powering the digital image capturer 102 , a computer 106 connected to the digital image capturer 102 via TCP/IP fast Ethernet connection, and monitors 108 .
  • the digital image capturer 102 is slidable along the working surface 14 with the X-ray emitter 18 , and includes optical elements for concentrating light and a digital imaging device such as a CCD chip, for capturing the image. Also included within image capturer 102 is at least one light sensor for initiating image capture when the X-ray emitter 18 is turned on, and for providing user feedback regarding the effective dose. Further details of the digital image capturer 102 are discussed later with reference to FIG. 4 .
  • the data is transferred to computer 106 for further processing and storage.
  • an operator can control various aspects and settings of the digital image capturer 102 , and organize the images in a database to record patient number, image capture date and user notes that may be relevant to the image.
  • the images have a dimension of 2048 rows by 3072 columns, and at 16-bit resolution, results in image sizes of about 12 megabytes.
  • the computer 106 can include mass storage devices such as a CD-Writer or DVD-Writer for making digital copies of the images for archiving or transfer, and can be networked for direct transfer via email or FTP to other practitioners for evaluation.
  • One monitor 108 can be located proximate to the operator for immediate viewing and analysis of the captured image, while another monitor 108 can be located in a different location for administrative and diagnostic purposes.
  • one computer 106 is shown connected to one digital image capturer 102 , however, multiple digital image capturers 102 can be controlled by the same computer 106 as each digital image capturer 102 can be separately addressable. Alternatively, multiple computers can be coupled to a single digital image capturer 102 .
  • a high quality printer can be coupled to computer 106 to print one or more copies of the image at any time.
  • image processing algorithms can be executed to enhance the view-ability of the image.
  • the images can be processed with available commercial software packages to add color to traditional black and white images to highlight specific organic materials, such as muscle, bone and tendons.
  • Digital image capturer 102 is mounted underneath working surface 14 and includes an X-ray grid 200 , a light shield 202 , an intensifying screen 204 , and imaging chamber 206 . Collectively, elements 200 , 202 and 204 form a light generator 205 . The dimensions of digital image capturer 102 are preferably constrained to a volume of 25 ⁇ 18 ⁇ 15 inches.
  • X-ray grid 200 and intensifying screen 204 can be the same as X-ray grid 25 and intensifying screen 28 respectively of FIG. 2 .
  • Light shield 202 can be constructed of bakelite or carbon fiber, but can also be made of any material that is opaque to light.
  • Bakelite and carbon fiber are preferred for their high transparency to X-rays.
  • the purpose of light shield 202 is to block all external light from entering imaging chamber 206 , as external light adds noise to the image, thus reducing image quality.
  • imaging chamber 206 should receive only light emitted from intensifying screen 204 .
  • Imaging chamber 206 is a rectangular volume having dimensions of about 18 ⁇ 23 inches by 15 inches. The chamber is sealed to prevent dirt and excessive humidity from entering the enclosure. Imaging chamber 206 is responsible for collecting and concentrating a maximum amount of emitted light from intensifying screen 204 .
  • imaging chamber 206 includes two planar reflectors 300 and 302 , a lens assembly 304 , and a CCD electronics board 306 .
  • the lens assembly 304 , and CCD electronics board 306 are components of the fast relay-optics system, for ensuring that the image being imprinted upon the CCD chip is effectively free of distortions and other image degradations.
  • reflectors 300 and 302 , and lens assembly 304 are positioned relative to each other such that the distance traveled by the light within imaging chamber 206 is maximized.
  • Imaging chamber 206 can include at least one light sensor 308 . It is noted that the CCD electronics board 306 is located outside the volume delimited by the grid 200 and the bottom of imaging chamber 206 . This is to ensure that the electronics are isolated from any X-rays that may pass into the imaging chamber 206 . Lens assembly 304 also includes a lead coating on surface 315 .
  • FIG. 4 As shown in FIG. 4 , light emitted from intensifying screen 204 is collected by a reflector 300 near the bottom of the imaging chamber 206 , and reflected across and up to a second reflector 302 positioned near the top left of imaging chamber 206 . The second reflector 302 then reflects the light into lens assembly 304 , which then applies corrections to the light before receipt by the CCD device mounted upon CCD electronics board 306 .
  • FIG. 5 is a top view of the imaging chamber 206 of FIG. 4 to illustrate the x-y co-ordinate positioning of reflectors 300 and 302 relative to the imaging chamber 206 .
  • two light sensors 308 are placed on either side of reflector 300 , and outside of the reflected light path.
  • the angles of reflector 300 and reflector 302 are set such that lens assembly 304 and CCD electronics board 306 is oriented in the y axis.
  • the angles of reflector 300 and reflector 302 could be set such that lens assembly 304 and CCD electronics board 306 could be oriented in any direction in the y-z plane.
  • Reflector 300 is normally flat but could also be curved in shape.
  • Reflector 302 is normally flat but could also be curved in shape.
  • the purpose of the reflectors is to position the CCD at an optimal distance from the intensifying screen while preserving image quality. At an optimal distance, it is possible to increase collection of light with larger lenses. Since the optimal distance of the light path varies between 27 and 30 inches, the preferred embodiment uses a combination of two reflectors organized in a three-dimensional configuration to position the CCD at such a distance within the defined size of the imaging chamber of the preferred embodiment, as shown in FIG. 5 .
  • reflector 300 plane is positioned at the bottom centre of the imaging chamber and redirects the light path to the top, left and back corner of the imaging chamber, where reflector 302 is located. Reflector 302 then redirects light path to the lens assembly located at the top left edge of the imaging chamber.
  • the 3-D light path coupled with the use of two reflectors allows for the design of smaller imaging chamber dimensions.
  • Both reflectors 300 and 302 are molded resin substrates or glass surfaces with an aluminum or equally reflective surface coating. In particular, by having reflector 302 disposed near the top of imaging chamber 206 , reflector 300 can be arranged at an angle of less than 45 degrees relative to the bottom surface of imaging chamber 206 .
  • lens assembly 304 and CCD electronics board 306 can be positioned at a bottom corner of the imaging chamber, and angled such that reflected light is received from appropriately angled reflector 302 .
  • Lens assembly 304 includes a series combination of lenses for correcting and focusing the light from reflector 302 onto an imaging device, such as a CCD chip.
  • the lens assembly 304 includes nine plastic and glass lenses, where select lenses can be aspherical or spherical in shape.
  • the designed lenses have the specific shapes that perfectly match the light path created by the reflector combination for the corrected field of view.
  • the spherical lenses are preferably made of glass or plastic while the aspherical lenses are made of plastic.
  • the sizes of the lens can be optimized to maximize light collection. Other designs may include as few as 5 lenses to as many as 15 lenses.
  • the lens assembly performs standard optical correction.
  • the distortions in the light path caused by reflectors 300 and 302 are fully corrected by the lenses within lens assembly 304 .
  • Spherical, linear and chromatic distortions can be corrected with the appropriate corrective lenses.
  • the lenses within lens assembly 304 have an optimized shape for optical aberration correction, including on-axis and off-axis aberrations.
  • the lens assembly 304 is designed to best match the size of the intensifying screen 204 to that of the CCD chip on the electronics board 306 .
  • the CCD sensor array size may not perfectly match the size of the intensifying screen 204 , adjustments to the lens assembly 304 can be made such that the image reduction ratio of the final image presented to the CCD chip matches the x and y dimensions of the CCD sensor array.
  • the lens assembly 304 can be quasi-monochromatic, meaning that only specific wavelengths of light are received by the CCD chip. While prior art systems try to provide a maximum amount of light to the CCD chip, the quasi-monochromatic system actually restricts the amount of light to the CCD chip.
  • FIG. 6 shows a wavelength spectrum demonstrating those wavelengths of light which are most relevant to digital X-ray image capture.
  • Wavelengths i through v represent 88% of the light energy that is available, where i represents the 425 nm to 475 nm range, ii represents the 480 nm to 510 nm range, iii represents the 530 nm to 570 nm range, iv represents the 580 nm to 610 nm range, and v represents the 615 nm to 630 nm range.
  • the contribution of wavelengths i, ii, iv and v are small, and eventually become dispersed over too many pixels at the intensifying screen edges.
  • the image sharpness cannot be effectively controlled, and image degradation results.
  • control of the image sharpness is facilitated across the entire area of the intensifying screen.
  • the image sharpness at the centre of the screen has been demonstrated to be less than 1 pixel wide, while the image sharpness at the edges of the screen has been demonstrated to be 1.25 pixels wide.
  • the spot size is consistently similar in size to a CCD pixel.
  • the consistent spot size across the entire area of the intensifying screen results in a sharper image across the entire image area.
  • a 2-cavity bandpass filter coating can be applied to the surface of any lens of lens assembly 304 .
  • the bandpass filter is made of thin dielectric layers, using materials such as Silicon Dioxide (SiO 2 ) and Zirconium Dioxide (ZrO 2 ).
  • the bandpass filter is transparent to wavelengths from 530 to 570 nanometers only, which includes photons of the main light peak of the intensifying screen, as shown in FIG. 6 . Those of the other peaks will be filtered out by the bandpass filter.
  • the main peak represents 55% of the total light energy emitted by the intensifying screen.
  • a bandpass filter of different materials, or with a different bandwidth, or with a different number of cavities may be used.
  • the CCD electronics board 306 can include standard components required for basic functionality of the mounted CCD chip, but can further include additional processing circuits, such as microprocessor, specifically a digital signal processor (DSP), to execute image processing algorithms.
  • Standard image processing algorithms can include noise suppression, flat fielding, dead pixel compensation and distortion correction, for example.
  • Such standard imaging processing algorithms are well known in the digital imaging field, and may require calibration of the CCD chip to generate calibration data such as pixel gain coefficients for flat fielding calibration, pixel non-uniformity and vignetting compensation of the digital image data. Dark noise data can be used for thermal noise compensation of the digital image data, dead pixel mapping data can be used for dead pixel compensation of the digital image data, and distortion data can be used for distortion correction of the digital image data.
  • the CCD electronics board 306 can include non-volatile memory such as Flash memory, for storing the data. Therefore, each digital image capturer 102 is pre-optimized during assembly, and executes the standard image processing algorithms transparently to the operator.
  • the Flash can also store an error log of anomalies or problems reported by the DSP or microprocessor, for access during diagnostic checks.
  • CCD electronics board 306 can include:
  • the method of FIG. 7 can be executed by the CCD electronics board 306 for capturing an image.
  • CCD electronics board 306 remains in standby mode, and no images are captured.
  • X-ray exposure has begun and the process for capturing the X-ray image begins.
  • the light sensors 308 detect light
  • the CCD chip begins charge accumulation.
  • a determination is made as to whether or not charge collection should terminate. This can be based on a configurable exposure time or on the X-ray exposure time duration. The method loops back to step 402 if the predetermined exposure time has not yet been reached and the light sensors are still detecting light.
  • the image is transferred from the CCD to the DSP at step 406 .
  • an optional dark image routine is executed, being a repeat of steps 402 to 406 , but for the same exposure time, except that no X-rays are emitted.
  • the dark image is subtracted from the previously collected image, to provide a net pre-processed image, which is then transferred to the computer 106 at step 412 .
  • the pre-processed image can then be subjected to a variety of post processing algorithms.
  • the raw data image can be processed to visually highlight specific tissues that the operator desires to see.
  • the image can be processed to improve viewability by adjusting sharpness, contrast and brightness.
  • the image viewability can be augmented through colorization through well known techniques.
  • the DSP or microprocessor can be configured to receive feedback from the light sensors 308 in order to control/optimize the image capture process.
  • the signal from the light sensors 308 can determine the particular image processing algorithm to apply in order to optimize viewability of image.
  • light sensors 308 can be used to initiate and end the image capture process.
  • CCD electronics board 306 is coupled to the computer via a communications cable
  • an alternate means for communication can include wireless transmissions according to well known standards, such as Bluetooth and WiFi.
  • the CCD electronics board 306 would be designed to include the appropriate transceiver circuits to enable wireless communication to the computer.
  • the CCD electronics board can include additional memory to provide temporary storage of images prior to transfer to the computer. Such memory is useful in applications where multiple images are captured during a session.
  • reflectors 300 and 302 , lens assembly 304 and CCD electronics board 306 are mounted to a supporting frame fixed to the imaging chamber 206 . While the supporting frame provides general alignment between the components, additional adjustment means can be incorporated to provide fine adjustment alignment. In alternate embodiments, the fine adjustment means can include manual adjustment components or X-ray tolerant electromechanical components that can be controlled to auto-adjust during maintenance checks. In an auto-adjusting embodiment, the adjustments can be calibrated to an intensity or positioning of light received by the sensor array of the CCD chip.
  • Light sensor 308 can be any commercially available device (photodiode, phototransistor, or other) installed within the imaging chamber and outside the path of light reflected by reflectors 300 and 302 .
  • Light sensor 308 is preferably connected to CCD electronics board 306 , and specifically to a DSP or microprocessor for execution of algorithms in response to the signal received from light sensor 308 .
  • a basic application of light sensor 308 is automatic activation of the CCD chip to begin image capture.
  • Another application is automatic exposure measurement by coupling light sensor 308 with a matched lens and arranged to collect light from specific areas of the intensifying screen 204 .
  • the light sensor 308 does not interfere with either the X-rays or light received by reflector 300 to reduce light collection efficiency.
  • the light sensor and matched lens can be arranged to collect light only from the pulmonary areas of an appropriately positioned patient.
  • the microprocessor can automatically terminate image capture and provide notification to the operator to stop X-ray emission once a sufficient amount of light has been received. Then the image data can be generated and sent to the microprocessor for image processing.
  • the microprocessor can be programmed to store predetermined image exposure parameters, such as light level thresholds, and to monitor the appropriate light sensors 308 .
  • the light sensors 308 provide a signal to the microprocessor, representing the received light level.
  • the microprocessor instructs the CCD chip to end image capture operations and send the image data. Accordingly, any number of light sensors 308 can be used in the imaging chamber 206 .
  • Advanced operations can be realized with light sensor 308 .
  • One such operation is multiple image capture from a single session.
  • a patient can be subjected to a predetermined dose while several images can be captured at different times during the session.
  • the CCD chip can be controlled to capture an image when predetermined thresholds of light have been reached.
  • Each predetermined threshold can be calibrated to correspond to a particular dose effective for highlighting a specific tissue. Therefore in a single session, multiple images highlighting specific tissues can be obtained.
  • the patient In contrast to film based systems, the patient must be subjected to multiple sessions in order to obtain the different images.
  • Another advanced operation is to provide feedback to the operator or system regarding the dose, and to calculate amounts by which the dose should be adjusted by in order to obtain the optimal image.
  • calibration data relating to light intensities corresponding to specific doses can be collected and stored in the microprocessor memory in the factory.
  • the light sensor 308 can provide feedback to the microprocessor for calculating an appropriate dose adjustment in order to obtain an optimal image.
  • the optimal image can depend on the tissue type of interest, brightness levels, and/or contrast levels.
  • the thresholds for comparing the session dose against can be pre-programmed in the microprocessor.
  • any suitable method for fixing the light sensor(s) 308 and corresponding matched lenses to the imaging chamber 206 can be used.
  • multiple light sensors 308 can be mounted to a rigid board, and a plastic sheet with integrated matched lenses aligned with each corresponding light sensor 308 can be overlaid on top of the board.
  • the components are inexpensive to purchase, fabricate and assemble.
  • the previously described components cooperate together to generate high quality digital images in a compact assembly.
  • the 3D configuration of reflectors 300 and 302 maximizes the light path length, which allows for flexible arrangement of reflectors 300 and 302 , and the use of larger lenses within lens assembly 304 .
  • the lenses within lens assembly 304 have an optimized shape for optical aberration correction, including on-axis and off-axis aberrations.
  • the lens assembly restricts the applied light to a specific wavelength range and applies optical correction to provide sharper images, and automatic exposure measurement feedback via one or more light sensors improves efficiency by automating the image capture process.
  • the digital image capturer 102 can obtain digital images having a quality equal or superior to prior digital X-ray systems at much lower costs. Due to its relatively compact size, the digital image capturer 102 can be easily used as a retro-fit for existing film-based X-ray machines, saving the clinic or hospital from costly replacement of the system. Furthermore, since most clinics employ computers to store patient information in databases, no additional computer is required, since the existing computer can be installed with the appropriate applications and software for communicating with the digital image capturer 102 . As previously mentioned, image processing algorithms can be integrated with the installed software, and updated as required. Furthermore, the computer can include software to perform diagnostic checks upon the system.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Physics & Mathematics (AREA)
  • Medical Informatics (AREA)
  • General Health & Medical Sciences (AREA)
  • Pathology (AREA)
  • Biomedical Technology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Optics & Photonics (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Molecular Biology (AREA)
  • Radiology & Medical Imaging (AREA)
  • Veterinary Medicine (AREA)
  • Biophysics (AREA)
  • Signal Processing (AREA)
  • General Physics & Mathematics (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • Public Health (AREA)
  • Multimedia (AREA)
  • Mathematical Physics (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Chemical & Material Sciences (AREA)
  • Analytical Chemistry (AREA)
  • Biochemistry (AREA)
  • Immunology (AREA)
  • Apparatus For Radiation Diagnosis (AREA)
  • Transforming Light Signals Into Electric Signals (AREA)
  • Conversion Of X-Rays Into Visible Images (AREA)
  • Radiography Using Non-Light Waves (AREA)
US11/000,533 2004-12-01 2004-12-01 Digital image collector for X-ray systems Expired - Fee Related US7289601B2 (en)

Priority Applications (11)

Application Number Priority Date Filing Date Title
US11/000,533 US7289601B2 (en) 2004-12-01 2004-12-01 Digital image collector for X-ray systems
CA2589341A CA2589341C (en) 2004-12-01 2005-11-29 Digital image collector for x-ray systems
NZ556259A NZ556259A (en) 2004-12-01 2005-11-29 Digital image collector for x-ray systems
MX2007006530A MX2007006530A (es) 2004-12-01 2005-11-29 Colector de imagen digital para sistemas de rayos x.
AU2005312295A AU2005312295B2 (en) 2004-12-01 2005-11-29 Digital image collector for X-ray systems
PCT/CA2005/001804 WO2006058420A1 (en) 2004-12-01 2005-11-29 Digital image collector for x-ray systems
JP2007543668A JP4937923B2 (ja) 2004-12-01 2005-11-29 Ｘ線システム用デジタル画像コレクタ
EP05814165A EP1829363A4 (en) 2004-12-01 2005-11-29 DIGITAL IMAGE COLLECTOR FOR X-RAY SYSTEMS
BRPI0520611-1A BRPI0520611A2 (pt) 2004-12-01 2005-11-29 coletor de imagem digital para sistemas raio-x; sistema de medição de auto-exposição para um coletor de imagem digital de raio-x e para obtenção de imagens de materiais
CNB2005800468063A CN100553302C (zh) 2004-12-01 2005-11-29 用于x射线系统的数字图像收集器
US11/763,103 US20070237297A1 (en) 2004-12-01 2007-06-14 Auto exposure measurement system for an x-ray digital image capturer

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102004001412.4 2004-01-09
US11/000,533 US7289601B2 (en) 2004-12-01 2004-12-01 Digital image collector for X-ray systems

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US11/763,103 Division US20070237297A1 (en) 2004-12-01 2007-06-14 Auto exposure measurement system for an x-ray digital image capturer

Publications (2)

Publication Number Publication Date
US20050151085A1 US20050151085A1 (en) 2005-07-14
US7289601B2 true US7289601B2 (en) 2007-10-30

Family

ID=36564712

Family Applications (2)

Application Number Title Priority Date Filing Date
US11/000,533 Expired - Fee Related US7289601B2 (en) 2004-12-01 2004-12-01 Digital image collector for X-ray systems
US11/763,103 Abandoned US20070237297A1 (en) 2004-12-01 2007-06-14 Auto exposure measurement system for an x-ray digital image capturer

Family Applications After (1)

Application Number Title Priority Date Filing Date
US11/763,103 Abandoned US20070237297A1 (en) 2004-12-01 2007-06-14 Auto exposure measurement system for an x-ray digital image capturer

Country Status (10)

Country Link
US (2) US7289601B2 (ko)
EP (1) EP1829363A4 (ko)
JP (1) JP4937923B2 (ko)
CN (1) CN100553302C (ko)
AU (1) AU2005312295B2 (ko)
BR (1) BRPI0520611A2 (ko)
CA (1) CA2589341C (ko)
MX (1) MX2007006530A (ko)
NZ (1) NZ556259A (ko)
WO (1) WO2006058420A1 (ko)

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20100266187A1 (en) * 2009-04-16 2010-10-21 Apteryx, Inc. Apparatus and method for virtual flaw removal from x-ray sensitive plates
CN102609542A (zh) * 2012-02-21 2012-07-25 云南电力试验研究院（集团）有限公司电力研究院 一种电力设备检测用x射线数字图像特征数据库
US11026646B2 (en) * 2018-02-07 2021-06-08 Illinois Tool Works Inc. Systems and methods for digital X-ray imaging

Families Citing this family (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP5711567B2 (ja) * 2011-02-28 2015-05-07 キヤノン株式会社 放射線画像撮影装置および放射線画像撮影のための装置
CN102429673B (zh) * 2011-09-09 2013-12-04 天津大学 一种模拟医用x光机数字化成像系统及其控制方法
CN103462627A (zh) * 2013-09-22 2013-12-25 江苏美伦影像系统有限公司 一种高灵敏度影像链系统
CN107192723B (zh) * 2016-03-14 2019-12-06 三菱电机株式会社 使用x射线的被检查对象物的判定装置以及判定方法
IT201600109999A1 (it) * 2016-11-02 2018-05-02 Eurotec Medical Systems S R L Apparato per densitometria ossea a raggi-x
CN106772530A (zh) * 2016-11-23 2017-05-31 江苏超敏仪器有限公司 术前束流剂量测量设备
CN108269043A (zh) * 2018-02-08 2018-07-10 王四春 一种跨境电商用一机双屏双控监控方法
CN110881111A (zh) * 2019-11-21 2020-03-13 杭州电子科技大学 一种小型化物体多角度x射线数字图像采集系统及方法
CN113514484B (zh) * 2021-07-13 2023-12-22 中国工程物理研究院激光聚变研究中心 适用于x射线成像的全光分幅系统

Citations (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4379348A (en) * 1980-09-23 1983-04-05 North American Philips Corporation X-Ray security screening system having magnification
US4736397A (en) 1985-12-16 1988-04-05 Applied Intellegent Systems, Inc. Radiation image inspection apparatus
US5138642A (en) 1989-03-02 1992-08-11 Innovative Imaging Systems, Inc. Detector imaging arrangement for an industrial CT device
US5187730A (en) * 1990-06-25 1993-02-16 Kabushiki Kaisha Toshiba X-ray diagnostic system and method of picking up X-ray picture
US5493600A (en) 1994-11-23 1996-02-20 Mcw Research Foundation Quality control film cassette for an x-ray imaging system
WO1996017265A1 (en) * 1994-11-28 1996-06-06 Aotec, Inc. Optical lens assembly
US5585638A (en) 1995-12-14 1996-12-17 General Electric Company X-ray detector for automatic exposure control of an imaging apparatus
US5712890A (en) 1994-11-23 1998-01-27 Thermotrex Corp. Full breast digital mammography device
US5723865A (en) 1994-11-23 1998-03-03 Thermotrex Corporation X-ray imaging device
US5790629A (en) * 1994-04-07 1998-08-04 Svensson; Stig Apparatus for making x-ray images
US5872595A (en) 1995-08-16 1999-02-16 Monahan; John F. Methods and apparatus for providing wide range exposure control for image intensifier cameras
US6047042A (en) 1998-03-25 2000-04-04 Continental X-Ray Corporation Automatic exposure and brightness control for fluoroscopic and radio-graphic imaging
JP2000183516A (ja) * 1998-12-15 2000-06-30 Matsushita Electric Ind Co Ltd Ｘ線実装検査装置及びそれを用いたｘ線実装検査方法
US6192105B1 (en) 1998-11-25 2001-02-20 Communications & Power Industries Canada Inc. Method and device to calibrate an automatic exposure control device in an x-ray imaging system
US6298109B1 (en) 1996-02-21 2001-10-02 Lunar Corporation X-ray imaging system
US6353657B1 (en) 1998-11-27 2002-03-05 Wuestec Medical, Inc. Image redirection and optical path folding
US6385289B1 (en) 1999-04-12 2002-05-07 Rigaku Corporation X-ray diffraction apparatus and method for measuring X-ray rocking curves
US6459765B1 (en) 2000-12-28 2002-10-01 Ge Medical Systems Global Technology Company, Llc Automatic exposure control and optimization in digital x-ray radiography
US6546076B1 (en) 2000-03-21 2003-04-08 Wuestec Medical, Inc. Digital high resolution x-ray imaging utilizing an imaging sensor
US20030142784A1 (en) 2000-04-06 2003-07-31 Makoto Suzuki X-ray inspection system
US6717174B2 (en) 1989-12-05 2004-04-06 University Of Massachusetts Medical Center System for quantitative radiographic imaging
US6778216B1 (en) * 1999-03-25 2004-08-17 Texas Instruments Incorporated Method and apparatus for digital camera real-time image correction in preview mode
US20040165095A1 (en) * 2002-09-25 2004-08-26 Seiko Epson Corporation Lens with infrared ray filter, method of manufacturing the same, and compact camera

Family Cites Families (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4186308A (en) * 1977-10-13 1980-01-29 Polaroid Corporation Large format photographic film cassette
JPH08191831A (ja) * 1995-01-19 1996-07-30 Morita Tokyo Seisakusho:Kk パノラマ式ｘ線撮影装置
GB2308935B (en) * 1996-01-06 2000-01-12 Marconi Gec Ltd A thermal imager referencing system
SE512202C2 (sv) * 1998-12-16 2000-02-14 Ao Medical Products Ab Digital bucky där jonkammare och raster kan fällas bort från detektorn
JP2000329898A (ja) * 1999-05-20 2000-11-30 Bitran Corp Ｘ線撮像装置
FR2798551B1 (fr) * 1999-09-14 2001-11-30 Eppra Dispositif de radiologie comportant des moyens d'agrandissement d'images perfectionnees
JP2003052680A (ja) * 2001-08-13 2003-02-25 Shimadzu Corp Ｘ線撮影装置

Patent Citations (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4379348A (en) * 1980-09-23 1983-04-05 North American Philips Corporation X-Ray security screening system having magnification
US4736397A (en) 1985-12-16 1988-04-05 Applied Intellegent Systems, Inc. Radiation image inspection apparatus
US5138642A (en) 1989-03-02 1992-08-11 Innovative Imaging Systems, Inc. Detector imaging arrangement for an industrial CT device
US6717174B2 (en) 1989-12-05 2004-04-06 University Of Massachusetts Medical Center System for quantitative radiographic imaging
US5187730A (en) * 1990-06-25 1993-02-16 Kabushiki Kaisha Toshiba X-ray diagnostic system and method of picking up X-ray picture
US5790629A (en) * 1994-04-07 1998-08-04 Svensson; Stig Apparatus for making x-ray images
US5493600A (en) 1994-11-23 1996-02-20 Mcw Research Foundation Quality control film cassette for an x-ray imaging system
US5712890A (en) 1994-11-23 1998-01-27 Thermotrex Corp. Full breast digital mammography device
US5723865A (en) 1994-11-23 1998-03-03 Thermotrex Corporation X-ray imaging device
WO1996017265A1 (en) * 1994-11-28 1996-06-06 Aotec, Inc. Optical lens assembly
US5872595A (en) 1995-08-16 1999-02-16 Monahan; John F. Methods and apparatus for providing wide range exposure control for image intensifier cameras
US5585638A (en) 1995-12-14 1996-12-17 General Electric Company X-ray detector for automatic exposure control of an imaging apparatus
US6298109B1 (en) 1996-02-21 2001-10-02 Lunar Corporation X-ray imaging system
US6047042A (en) 1998-03-25 2000-04-04 Continental X-Ray Corporation Automatic exposure and brightness control for fluoroscopic and radio-graphic imaging
US6192105B1 (en) 1998-11-25 2001-02-20 Communications & Power Industries Canada Inc. Method and device to calibrate an automatic exposure control device in an x-ray imaging system
US6353657B1 (en) 1998-11-27 2002-03-05 Wuestec Medical, Inc. Image redirection and optical path folding
JP2000183516A (ja) * 1998-12-15 2000-06-30 Matsushita Electric Ind Co Ltd Ｘ線実装検査装置及びそれを用いたｘ線実装検査方法
US6778216B1 (en) * 1999-03-25 2004-08-17 Texas Instruments Incorporated Method and apparatus for digital camera real-time image correction in preview mode
US6385289B1 (en) 1999-04-12 2002-05-07 Rigaku Corporation X-ray diffraction apparatus and method for measuring X-ray rocking curves
US6546076B1 (en) 2000-03-21 2003-04-08 Wuestec Medical, Inc. Digital high resolution x-ray imaging utilizing an imaging sensor
US20030142784A1 (en) 2000-04-06 2003-07-31 Makoto Suzuki X-ray inspection system
US6459765B1 (en) 2000-12-28 2002-10-01 Ge Medical Systems Global Technology Company, Llc Automatic exposure control and optimization in digital x-ray radiography
US20040165095A1 (en) * 2002-09-25 2004-08-26 Seiko Epson Corporation Lens with infrared ray filter, method of manufacturing the same, and compact camera

Non-Patent Citations (2)

* Cited by examiner, † Cited by third party
Title
Melles Griot "The Practical Application of Light" 1999, pp. 13.26, 13.27, 13.39. *
Melles Griot (1999) "The Practical Application of Light" pp. 13.26, 13.27, 13.29. *

Cited By (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20100266187A1 (en) * 2009-04-16 2010-10-21 Apteryx, Inc. Apparatus and method for virtual flaw removal from x-ray sensitive plates
US8265369B2 (en) * 2009-04-16 2012-09-11 Apteryx, Inc. Apparatus and method for virtual flaw removal from X-ray sensitive plates
CN102609542A (zh) * 2012-02-21 2012-07-25 云南电力试验研究院（集团）有限公司电力研究院 一种电力设备检测用x射线数字图像特征数据库
CN102609542B (zh) * 2012-02-21 2014-01-01 云南电力试验研究院（集团）有限公司电力研究院 一种电力设备检测用x射线数字图像特征数据库
US11026646B2 (en) * 2018-02-07 2021-06-08 Illinois Tool Works Inc. Systems and methods for digital X-ray imaging
US11026645B2 (en) 2018-02-07 2021-06-08 Illinois Tool Works Inc. Radiography backscatter shields and X-ray imaging systems including backscatter shields
US11596370B2 (en) 2018-02-07 2023-03-07 Illinois Tool Works Inc. Systems and methods for digital x-ray imaging
US11690583B2 (en) 2018-02-07 2023-07-04 Illinois Tool Works Inc. Systems and methods for digital x-ray imaging

Also Published As

Publication number Publication date
BRPI0520611A2 (pt) 2009-06-13
JP4937923B2 (ja) 2012-05-23
EP1829363A4 (en) 2008-06-18
CA2589341A1 (en) 2006-06-08
CN101103622A (zh) 2008-01-09
CA2589341C (en) 2013-04-23
AU2005312295A1 (en) 2006-06-08
NZ556259A (en) 2010-01-29
AU2005312295B2 (en) 2010-04-29
EP1829363A1 (en) 2007-09-05
JP2008521521A (ja) 2008-06-26
US20050151085A1 (en) 2005-07-14
MX2007006530A (es) 2007-08-02
US20070237297A1 (en) 2007-10-11
CN100553302C (zh) 2009-10-21
WO2006058420A1 (en) 2006-06-08

Similar Documents

Publication Publication Date Title
CA2589341C (en) Digital image collector for x-ray systems
US10813617B2 (en) Radiation emitting device, method for controlling radiation emitting device, and program
CA2534947C (en) Camera and method for optically capturing a screen
US10709406B2 (en) Radiography apparatus, method for controlling radiography apparatus, and program
US7555100B2 (en) Long length imaging using digital radiography
JP6208600B2 (ja) 放射線画像撮影装置および放射線画像撮影システム
US5712890A (en) Full breast digital mammography device
US7924982B2 (en) Radiographic imaging apparatus and control method thereof
US8160207B2 (en) Radiation imaging apparatus
JP2007199079A (ja) Ｘ線撮像装置
US20040161075A1 (en) Radiographing apparatus
US9561008B2 (en) Method of displaying image
EP1833371B1 (en) X-ray converter
JP2005007061A (ja) 画像処理装置、画像処理システム、画像処理方法、記憶媒体、及びプログラム
KR101012506B1 (ko) 디지털 엑스레이 촬영방법 및 엑스레이 촬영장치
JP6739511B2 (ja) 放射線画像撮影装置および放射線画像撮影システム
JP4016580B2 (ja) 放射線撮影装置
JP2018023794A (ja) 放射線画像撮影装置および放射線画像撮影システム
JP2020127802A (ja) 放射線画像撮影装置および放射線画像撮影システム
JP2005066144A (ja) Ｘ線画像撮影装置
JP2005270260A (ja) Ｘ線撮影装置
JP2012070858A (ja) 散乱ｘ線除去用グリッド
JP2005017513A (ja) 放射線画像撮影装置
JP2013221897A (ja) 放射線撮影装置

Legal Events

Date Code Title Description
AS Assignment

Owner name: IMASCCOPE INC., CANADA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:CASEAULT, JEAN;WANG, MIN;THIBAULT, SIMON;REEL/FRAME:016041/0391

Effective date: 20041130

STCF Information on status: patent grant

Free format text: PATENTED CASE

FPAY Fee payment

Year of fee payment: 4

FPAY Fee payment

Year of fee payment: 8

AS Assignment

Owner name: IMASIGHT, INC., CANADA

Free format text: CHANGE OF NAME;ASSIGNOR:IMASCOPE INC.;REEL/FRAME:038684/0616

Effective date: 20070605

AS Assignment

Owner name: BIOKINEMETRICS, INC., IOWA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:DELOITTE RESTRUCTURING INC. (TRUSTEE OF IMASIGHT INC.);REEL/FRAME:038715/0128

Effective date: 20151222

FEPP Fee payment procedure

Free format text: MAINTENANCE FEE REMINDER MAILED (ORIGINAL EVENT CODE: REM.); ENTITY STATUS OF PATENT OWNER: SMALL ENTITY

LAPS Lapse for failure to pay maintenance fees

Free format text: PATENT EXPIRED FOR FAILURE TO PAY MAINTENANCE FEES (ORIGINAL EVENT CODE: EXP.); ENTITY STATUS OF PATENT OWNER: SMALL ENTITY

STCH Information on status: patent discontinuation

Free format text: PATENT EXPIRED DUE TO NONPAYMENT OF MAINTENANCE FEES UNDER 37 CFR 1.362

FP Lapsed due to failure to pay maintenance fee

Effective date: 20191030